Process for demineralization of bone matrix with preservation of natural growth factors

ABSTRACT

A demineralized bone matrix is produced by a process in which a bone body is placed in a first processing solution comprising an acid to demineralize the bone body. The bone body is periodically removed from the first solution at specific time intervals to perform at least one test, such as a compression test, on a mechanical property of the bone body. When the test yields a desired result, the bone body is exposed to a second processing solution that is less acidic than the first, thus minimizing the exposure of the bone body to the harsh acidic conditions of the demineralization phase of the process.

CROSS-REFERENCE TO RELATED APPLICATION(S)

This application is a continuation of application Ser. No. 13/453,818,filed on Apr. 23, 2012, which is a divisional application of applicationSer. No. 12/130,384, filed May 30, 2008, which issued as U.S. Pat. No.8,574,825 on Nov. 5, 2013, which claims benefit from Application Ser.No. 60/932,848, entitled PROCESS FOR DEMINERALIZATION OF BONE MATRIXWITH PRESERVATION OF NATURAL GROWTH FACTORS, filed Jun. 1, 2007, each ofwhich is incorporated by reference in their entirety.

BACKGROUND

The present invention relates to a process for manufacturingdemineralized bone matrix. More specifically, the present inventionrelates to a method for manufacturing demineralized bone matrix, whichfocuses on the preservation of native/intrinsic growth factors residingwithin the matrix while providing unique handling characteristics. Thedemineralized bone matrix will be used in promoting bone and cartilagerepair and bone and cartilage growth and regeneration.

Approximately one million bone graft procedures are conducted each yearthroughout the world. About 500,000 of these procedures are conducted inthe United States, and roughly 250,000 of the bone grafting proceduresin the United States involve the spine. These bone graft and bonesubstitute products may include, for example, bone substitutes, bonedowels, demineralized bone matrix products, including putties,‘platelet” helpers, and other allograft bone materials.

Injury to the cartilage of the knee joint is also a common orthopedicproblem, affecting millions of people in the United States. Damagedarticular cartilage does not normally regenerate itself. Currenttreatment for cartilage damage requires patients to undergo arthroscopicsurgery to relieve their symptoms. If the cartilage cannot be repaired,and must be removed, the patient is likely to develop osteoarthritis,with possible need for further surgeries, including total kneereplacement in severe cases.

The use of bone materials to promote bone healing after facture, boneloss, infection, tumor, or other pathologic conditions is well known tothose skilled in the art. Typically, bone grafting employs one of threemodalities to promote bone healing. First, an autologous bone graft maybe used. An autologous bone graft is derived from the recipient and iscommonly taken from the iliac bone. Second, a bone allograft may be usedwhich refers to a graft derived from a separate donor, usually withinthe same species. Finally, a bone graft substitute may be used that isnaturally derived (e.g., from bone chips, granulated bone powder, andthe like) or, in the alternative, synthetic or semi-synthetic products,generally in the form of putty and gel type of defect fillers, made upof allogeneic bone chips, granules, or bone powder, with or withoutcarriers.

Autologous bone graft, sometimes referred to as an autograft (i.e., thepatient's own bone), may be harvested to supply the needed bone torepair the defect. As appreciated by those skilled in the art, there aremany advantages for using autologous bone in bone defect repair. Forexample, autologous bone is typically viscoelastic, osteoconductive,osteoinductive, and osteogenic (i.e., contains cells in its matrix thatpromote bone formation). In addition, an autologous bone graft avoidshistocompatibility and infectious disease issues. Autologous bone,however, is limited in supply, is generally painful to the patient uponharvesting, and may lead to significant donor site morbidity (i.e., mayrequire additional surgical incisions in the patient, may lead tosurgical complications, blood loss and may cause additional patientdiscomfort, and may ultimately increase patient recovery time).

Allograft bone grafts are advantageous from the standpoint of beingavailable in larger quantities compared to autologous bone grafts.However, allograft bone grafts may present disadvantages relating tohistocompatibility issues (e.g., rejection by recipient immune system),the potential harboring of infectious agents, and may also include bonewith poor malleable or mechanical characteristics (e.g., elasticity,compressibility, resiliency, and the like) due to high calcium andmineral content. Presently available bone graft substitutes developed bythose skilled in the art usually have many of the same disadvantages asoutlined above with regards to allograft bone grafts. Bone allograft orsynthetic graft substitute products are generally formulated as puttyand gel type fillers, designed to be inserted into dead space (s)between bone defects (i.e., defect or void fillers). Traditionally, bonegraft substitutes may be made from allogeneic bone chips, granules, orbone powder, or synthetic materials with or without carriercompositions. Additionally, there are a few xenogeneic bone graftproducts available that are made from bovine bone, and the presentinvention may be adapted to use other sources of starting material, suchas bovine material. Disadvantages are similar to that presented withallografts, including potential immune reaction to xenogeneic bone andinfectious agents, including prions.

Another significant disadvantage of the currently available autograft,allograft, and bone substitute products of the prior art is that theyare generally unable to resist loading forces and maintain their shapeand structural integrity during surgical use for bone repair. To date,no solid, pre-shaped, flexible, elastic product (bone-derived orsynthetic) that is able to resist loading forces, deform and then regainits shape and structural integrity is available for surgical use. Thesecharacteristics are essential for producing bone repair that closelymimics the normal bone condition in the absence of the bone defect.

In addition, bone graft materials and bone graft substitutes are knownto have structural, mechanical and biological characteristics (e.g.,lack of compressibility, lack of elasticity, and the like), which hindertheir surgical placement, require relatively invasive surgicalprocedures, or sub-optimally promote bone growth.

Some bone allograft materials or synthetic composites, includingceramics and allograft bone material, have attempted to mimic certainautograft characteristics. For example, prior art ceramic bone graftsubstitutes, such as tri-calcium phosphate compounds, haveosteoconductive activity (i.e., facilitates formation of bone trellisstructure by promoting vascularization), but do not have osteoinductiveactivity (i.e., possess bone morphogenetic proteins that facilitateformation of bone by active recruitment of stem cells from surroundingtissue). Moreover, it has been found that ceramic bone graft substitutesof the prior art may be brittle or fail under forces of compression,torsion, bending, and/or tension.

Prior art bone graft substitutes, including demineralized cortical bonepowder and recombinant human bone morphogenic protein (rhBMP), aretypically osteoinductive. These bone graft substitutes, however, lackosteoconductive properties and generally have no macrostructure toencourage cell ingrowth and sufficiently resist the forces ofcompression, torsion, bending, and/or tension. Although larger sizedtraditional allograft bone products are osteoconductive and have some ofthe mechanical strength properties of bone, they are less osteoinductivedue to their mineral content, cortical structure, and overall density.To date, no grafting material exists that can be deformed, for examplecompressed, torqued, and/or bent, which possess the mechanicalproperties to allow it to regain its original shape, structure, andsize.

Demineralized cortical bone matrix (DBM) putties developed by thoseskilled in the art commonly include very small (e.g., micron-sized)particles of cortical allograft bone (e.g., demineralized,nondemineralized, or both) mixed with a carrier to produce a workableputty or gel in varying viscosities. Prior art bone substitute compounds(e.g., putties, gels, solutions, and the like) may be introduced into abone defect with a spatula, syringe or by hand. Since these prior artbone substitute compounds are malleable, they generally deform to fitirregular spaces. However, since the active particles are typicallymicron-sized, bone substitute putties, gels, solutions, and the like maynot resemble normal bone macroscopically and, in addition, may notcontain normal pores, surfaces, spaces, and bone architecture. Moreover,the carriers used in prior art bone substitute compounds generally holdthe micron-sized particles in suspension or in a colloid that tends todegrade with time, leaving the construct without normal bonymacro-structure. For example, under in vivo conditions and in thepresence of saline, blood, and/or blood serum, and during irrigation,many of these bone substitute compounds (e.g., putties, gels, solutions,and the like) breakdown, dissolve, or ooze out of the bone void at thetime of surgery or within minutes or hours after their introduction intothe bone defect. Even those prior art bone substitute compounds that donot dissolve in vivo do not resemble normal bone in macro-structure.

In addition, the bone substitute compounds of the prior art may notmaintain the general mechanical properties (e.g., elasticity,flexibility, resistance to compression, tension, torsion, bending, orthe like) normally attributed to bone. To this end, there are no bonesubstitute compounds available that can be compressed into a bone voidor into a metallic, plastic, or composite implanted matrix with theability to expand to fit that void and in the process of expansionregain its respective micro and macro shape and size through maintenanceof its physical properties or memory.

Studies of demineralized bone products have shown a great variability inosteoinductive potential as measured by various bioassays, including theALP assay, native/intrinsic BMP levels evaluated by extraction and ELISAassay, and in vivo measures of bone fusion. Factors contributing to thisvariability may include differences in processing techniques. Variedcurrent practices of delipidification, demineralization and terminalsterilization of bone have the potential to significantly and negativelyaffect native growth factors contained within the bone matrix. Chemicalprocessing of bone matrix with prolonged exposure to high concentrationsof acid or high levels of gamma irradiation all reduce osteoinductiveactivity of the treated bone. Current practices include demineralizationprocesses that monitor solution pH changes during acid exposure andutilize set concentrations and exposure times to acid. None of thecurrent practices are optimized to preserve native growth factorsassociated with the bone matrix by reducing exposure to acid. Inaddition, there is structural variability within cancellous bone foundat different sites within the body and between donors (i.e. variation inporosity and density). Such variations significantly affectdelipidification and demineralization processing outcomes, even betweencancellous bone blocks of the same size. Currently, most experts in theart believe cancellous bone to be only osteoconductive and notosteoinductive (Schwarz 1991, Arch Orthop Trauma Surg.) (Finkemeier2002, J. Bone Joint Surg.). This perception is maintained by processingmethods that remove, or render inactive, osteoinductive growth factors.The present invention produces a cancellous bone matrix with higherquantities of active growth factors than current art processes. Oneskilled in the art would recognize that a process that minimizesexposure of the bone matrix to potential damaging agents duringprocessing, optimized to preserve native growth factor levels, would bea considerable advance in the field.

Ozone is a gas with known lethal effects on microorganisms and resultantsterilizing properties that are used extensively in the water and foodindustries. Ozone is a strong bactericide needing only a few microgramsper milliliter for kill of organisms including aerobic and anaerobicbacteria such as: Bacteroides, Campylobacter, Clostridium,Corynebacteria, Escherichia, Klebsiella, Legionella, Mycobacteria,Propriobacteria, Pseudomonas, Salmonella, Shigella, Staphylococcus,Streptococcus, Yersinia, and Mycobacteria. It is also effective againstviruses, including Flaviviridae, Filoviridae, Hepnaviridae,Herpesviridae, Orthomyxoviridae, Retroviridae. Coronaviridae,Togaviridae, Rhabdoviridae, Bunyaviridae, Pramyxoviridae, andPoxviridae. Non-enveloped susceptible viral families include:Adenoviridae, Picornaviridae, Papillomaviridae, Caliciviridae,Astroviridae, and Reoviridae. Ozone neutralizes microorganisms via aspectrum of mechanisms. Most-studied is ozone oxidation of bacteriallipids and proteins found in bacterial cell membranes, and viralenvelope lipids, phospholipids, cholesterols, and glycoproteins. Ozoneis also toxic to mammalian cells although the mechanisms are notcompletely understood. Application of ozone in the process of creatingdemineralized bone matrix has the potential for several improvementsover currently available bone products, including bioburden reduction,sterilization, whitening of the bone, delipidification, and makinggrowth factors within the matrix more available.

To date, those skilled in the art have been unsuccessful in theirattempts to overcome the above-identified disadvantages associated withknown and available prior art bone substitute compounds. In particular,those skilled in the art have been unsuccessful in identifying andproducing bone grafting materials that mimic certain normal bonecharacteristics by having improved malleable or mechanical properties.In this regard, there is a need in the art for a bone replacement and/orgrowth enhancement product that (1) precisely mimics normal bonearchitecture in order to serve as a conduit for vascular and cellimmigration; (2) is malleable and elastic; and (3) resists compression,tension, torsion, and bending forces, without fracturing and whendeformed has the ability to regain its original shape, structure andsize. Therefore, as readily appreciated by those skilled in the art,novel demineralized bone matrices, compositions, and methods forpromoting the repair of bone defects that address the disadvantages ofthe known prior art would be a significant advancement in the art. Thesematrices have clinical application not only for bone void healing andbone regeneration, but also for cartilage regeneration by providingscaffolding and growth factors to stimulate growth of new tissue in acartilage defect.

In the presence of saline or body fluids, a bone graft compound that canbe compressed to fill a void (in bone or cartilage), which does notdissolve or decompose, and which retains its macro-structure for days orweeks would be a significant advancement in the art. Moreover,demineralized cancellous bone matrices that are osteoinductive,osteoconductive, bioresorbable, biocompatible, substantially similar instructure to bone or cartilage, easy to use and which reduce patientmorbidity, and are cost-effective to manufacture would also be asignificant advancement in the field.

In addition, there is also a need in the art for demineralized bonematrices that can be used in association with progenitor cells that canbe injected and infiltrated into its porous structure to allowattachment, differentiation, proliferation and ultimately function toregenerate new tissue when transplanted or to serve as a 3-D cellculture environment for research and drug screening.

Finally, demineralized bone matrix can also be utilized as a carrier forbioactive agents, attached to the matrix surface by way of a coating,injection or impregnation, designed to release active biologic growthfactors or pharmacologic agents immediately or over time. This would bea further advancement over the known prior art.

SUMMARY

The present invention is a method for producing an osteoinductive andosteoconductive demineralized bone matrix. Due to the structuralvariability of cancellous bone found at different sites within the bodyand between donors (i.e. variation in porosity and density), nopreviously described process can consistently produce desired physicalproperties while limiting the amount of acid exposure, thus minimizingdamage to growth factors during demineralization. This inventiondescribes a process in which a bone body is placed in a first processingsolution comprising an acid to demineralize the bone body. The bone bodyis periodically removed from the first solution at specific timeintervals to perform at least one test, such as a compression test, on amechanical property of the bone body. When the test yields a desiredresult, the bone body is exposed to a second processing solution that isless acidic than the first, thus minimizing the exposure of the boneblock to the harsh acidic conditions of the demineralization phase ofthe process.

BRIEF DESCRIPTION OF THE DRAWINGS

FIGS. 1 a and 1 b are photographs illustrating an exemplary embodimentof a demineralized cancellous bone matrix produced by the presentinvention. FIG. 1 a shows the demineralized bone matrix in a compressedstate, FIG. 1 b shows the demineralized bone matrix in a non-compressedstate. It can be seen that the compressible nature of the resultinggraft allows the demineralized bone matrix to be inserted into a bonedefect void in a compressed state with the graft expanding to optimallyfill the contours of the bone defect void when the compression force isremoved.

FIG. 2 is a chart, which represents levels of insulin-like growthfactor-1 (IGF-1) in three samples of demineralized cancellous bonematrix from the same donor after subjecting the three samples todifferent demineralization protocols. Samples A and B representdemineralized cancellous bone matrix produced according to theprocesses, methodologies, and techniques of the present invention.Sample C represents demineralized cancellous bone matrix producedaccording to the state of the prior art found in the literature,demonstrating damage or removal of IGF-1.

FIGS. 3 a-3 c illustrate the effect of acid exposure on the levels ofnative growth factors in demineralized cancellous bone. FIG. 3 aillustrates the effect of acid exposure on BMP-2. FIG. 3 b illustratesthe effect of acid exposure on BMP-4. FIG. 3 c illustrates the effect ofacid exposure on BMP-7. Sample A represents the growth factor content ofdemineralized cancellous bone matrix processed according to a preferredembodiment of the present invention, showing higher levels of BMPsversus samples B and C. Sample B represents the growth factor content ofdemineralized cancellous bone matrix processed according to methodscurrently being practiced in the industry, showing reduced levels ofBMPs in comparison with sample A representing the current invention.Sample C represents the growth factor content in demineralizedcancellous bone matrix processed by exposure to acid for 24 hours,demonstrating damage or removal of BMPs.

FIGS. 4 a-4 c illustrate the increase in detectable growth factors indemineralized cancellous bone matrix after exposure of the demineralizedcancellous bone matrix to ozonated solution for 20 minutes or 3 hours,as compared to an unozonated (control). FIG. 4 a illustrates theincrease of BMP-2. FIG. 4 b illustrates the increase of BMP-4.

FIG. 4 c illustrates the increase of BMP-7. The results demonstrate thatozone exposure resulted in greater levels of extracted BMPs obtainedfrom the matrix as measured by ELISA.

FIGS. 5 a-5 c illustrate the decrease in detectable growth factors indemineralized cancellous bone matrix after exposure of the demineralizedcancellous bone matrix to a solution of hydrogen peroxide and water for15 minutes or 1 hour, as compared to the control. FIG. 5 a illustratesthe decrease of BMP-2. FIG. 5 b illustrates the decrease of BMP-4. FIG.5 c illustrates the decrease of BMP-7. The results demonstrate thathydrogen peroxide exposure resulted in lower levels of extracted BMPsobtained from the matrix as measured by ELISA.

DETAILED DESCRIPTION

Unless otherwise defined, the technical, scientific, and medicalterminology used herein has the same meaning as understood by thoseskilled in the art. However, for the purposes of establishing supportfor various terms that are used in the present application, thefollowing technical comments, definitions, and review are provided forreference.

The term “osteoconductive” as used herein refers to a material thatfacilitates the spontaneous formation of bone by furnishing amicroenvironment that supports the ingrowth of blood vessels,perivascular tissue and osteoprogenitor cells into the site where it isdeposited

The term “osteoinductive” refers to substances within the bone matrixthat actively trigger the formation of bone. Osteoinductive materialpromotes the recruitment of osteoprogenitor cells from an ectopic or anorthotopic site and stimulates their proliferation and differentiationinto bone-forming cells, i.e. osteoblasts.

The term “osteogenic” as used herein refers to a substance containinglive osteoprogenitor cells in its matrix that actively promote new boneformation.

The term “matrix” as used herein refers to an extracellular matrix ofcancellous bone remaining after demineralization. The highly porouscancellous bone matrix provides scaffolding conducive for cellattachment and tissue regeneration.

The term “BMP(s)” as used herein refers to bone morphogeneic proteinsthat have been associated with bone and cartilage growth through themechanism of providing signals to osteogenic cells to differentiate,proliferate and regenerate new tissue.

The term “growth factors” as used herein refers to known proteins andhormones that promote neovascularization and growth of new tissue.

In an exemplary embodiment, a demineralized cancellous bone matrix thatpromotes bone healing, arthrodesis, new bone formation, and repair ofpathologic non-union.

Preferably, the demineralized cancellous bone matrix is comprised of oneor more large-sized constructs (e.g., 2 mm to several centimeters) ofintact demineralized cancellous bone with a residual mineral contentless than two percent (<2%).

The novel demineralized cancellous bone matrices of the presentinvention provide unique and valuable mechanical properties whileminimizing damage to (or removal of) native growth factors duringdemineralization. In an exemplary embodiment, cancellous bone pieces areprocessed in an acid solution until the bone pieces are compressible to5 to 60 percent of their original shape while minimizing deteriorationto, inactivation of, or elimination of growth factors, intrinsicallypresent in cancellous bone, by removing each cancellous bone piece froma demineralizing acid solution, at specific time intervals, in order tomeasure compression properties. When each piece is compressible to saidpercent range, it is prevented from further exposure to the acidicsolution by placing it in (or rinsing with) a solution having a pHgreater than 4.

In another exemplary embodiment, cancellous bone pieces are processed inan acid solution until they contain less than 2 percent residual calciumby weight and the bone pieces are compressible to 5 to 60 percent oftheir original shape, while minimizing deterioration to, inactivationof, or elimination of growth factors, intrinsically present incancellous bone.

In an additional exemplary embodiment, cancellous bone pieces areprocessed in an acid solution until the bone pieces are compressible toless than 60 percent of their original shape, using between 10 and 1000grams-force/cm², while minimizing deterioration to, inactivation of, orelimination of growth factors, intrinsically present in cancellous bone.Each cancellous bone piece is removed from a demineralizing acidsolution, at specific time intervals, in order to measure compressionproperties, such that when each piece is compressible to said percentrange it is prevented from further exposure to the acidic solution byplacing it in (or rinsing with) a solution with a pH greater than 4.

In another exemplary embodiment, cancellous bone pieces are processed inan acid solution in order to demineralize the bone bodies. Periodicallythe bone is removed in order to measure the compression force versus thepercentage of size reduction when the bone body is under the compressionforce. The result of the compression force versus the compressed sizedetermines the next step in the bone processing. The outcome of thetesting determines both the acid concentration the bone body will nextbe soaked in and the time period for which it will be soaked before thecompression force and compressed size are measured again. This step isrepeated until the bone body is compressible to 5 to 60 percent, of itsoriginal shape, using between 10 and 1000 grams-force/cm². This processminimizes deterioration to, inactivation of, or elimination of growthfactors, intrinsically present in cancellous bone, by removing eachcancellous bone piece from a demineralizing acid solution, at specifictime intervals, in order to measure compression properties. When eachpiece is compressible to the aforementioned percent range, it isprevented from further exposure to the acidic solution by placing it in(or rinsing/spraying/dipping/soaking with) a solution having a pHgreater than 4.

Furthermore, the physical and chemical characteristics and structure ofthe demineralized bone matrices of the present invention allow forcoating or impregnating bioactive agents, including growth factors, thatare designed to elute into the surrounding tissues. In an exemplaryembodiment, the surface of the demineralized bone matrix may be inimmediate contact with the surrounding host tissues and fluids. Sincethe demineralized bone matrix maintain normal bone shape and structure,it will not dissolve and ooze from a bone defect, void, or mechanicaldevice to which it may be applied for insertion into said bone defect orvoid. Since the demineralized bone matrix has an open porous structure,active proteins present on the surface of the matrix are not hidden fromthe host environment by a carrier that are typically present in puttiesand gels. There is no dilution of the bone by carriers, therefore thedemineralized bone matrix graft will have a higher content of bonecompared with currently available putties and gels that are often lessthan 30% total bone content.

An exemplary embodiment of the present invention may be directed to amethod of cutting, shaping, or molding the demineralized cancellous bonematrix to fit specific shapes and contours needed to conform toassociated mechanical devices like spinal cages, acetabular cups, tubes,and cylinders. In addition, the present invention is directed todemineralized cancellous bone matrices that can be used alone as ascaffold or bone void filler, or in conjunction with other metallic,plastic, or composite devices, relying on its biologic and mechanicalcharacteristics to promote bone healing, fill a space, to maintain itsessential structure, and bridge separate bony surfaces withoutfracturing or failing under compressive, tensile, bending, or torsionalloads.

As noted above, the demineralized cancellous bone matrices of thepresent invention may be configured to fit inside a mechanical devicelike a spinal cage. If engageably introduced into a mechanical devicelike a spinal cage dry, the demineralized cancellous bone matrix willexpand in the device when hydrated to completely fill the device withtight apposition against host bone on either side of the mechanicaldevice. Accordingly, the demineralized cancellous bone matrix may becompressed to fit into the irregularities that can often result frombone loss due to cystic change, degeneration of bone, osteoporosis, orprosthetic revision between bone and an artificial joint implant like anacetabular cup, femoral stem, or other arthroplasties. When compressed,the demineralized cancellous bone matrix will tend to reversibly deformto fit the surrounding contours, but with its elasticity, it will expandto fill adjacent voids without oozing out of the bony defect or void.

Special physical properties of the demineralized bone matrix mayinclude, for example: (1) volume change with hydration, elasticity tocompression, tension, torsion, bending, and compressibility, etc.; (2)different physical characteristics depending on whether thedemineralized bone matrix are hydrated or non-hydrated; (3) capable ofmixing with blood, bone marrow aspirate, blood products, and the like;(4) expanding with hydration to fill a void without losing its tensileproperties; (5) will not dissolve with irrigation or time like otherprior materials such as putties, devices and methods; (6) will not loseits tensile properties when infiltrated by body fluids; (7) capable ofconforming to irregular shapes without fracturing or losing basicbiologic attributes; (8) capable of absorbing blood and fluid and expandwith hydration; and (9) capable of tolerating cyclic loading in tension,compression, bending and torsion without early fatigue fracture.

The present invention demonstrates improved biological properties inpromoting bone repair and growth. Optimized processing of thedemineralized bone matrix will allow for retention of native growthfactors and yields a matrix that has higher growth factor levels andenhanced osteoinductive properties. The demineralized bone matrices, inaccordance with the present invention, may be osteoinductive,osteoconductive, osteogenic, and combinations thereof. The highly porousnature of the demineralized cancellous bone matrix results in a naturalscaffold for cell attachment and other cellular activities that lead totissue regeneration. Cells from the patient, including osteoprogenitorcells, readily attach to the demineralized cancellous bone matrix andgrow new tissue. Moreover, the demineralized bone matrices may haveuniversal application in many bone graft procedures, for example and notby limitation, orthopedic surgery, neurological surgery, plasticsurgery, dental surgery, dermatologic surgery, and the like.

A further improvement in the design and function of the presentinvention is the use of ozone in the processing protocol for severalpurposes, including enhanced availability of growth factors includingBMPs that are associated with the collagen matrix followingdemineralization, enhanced delipidification and whitening of the matrixduring processing, and decontamination and sterilization of the matrix.

In addition, demineralized cancellous bone matrices of the presentinvention may have application to many disease states, for example andnot by limitation, spine fractures and disc degeneration, osteoporosisor osteopenia, orthopedic fracture and joint degeneration, cartilagerepair, dental procedures, and the like.

An exemplary embodiment of the present invention includes the use of thedemineralized cancellous bone matrices prepared in accordance with theprocesses, methodologies, and techniques of the present invention may beused as material for the 3-D culturing of cells, including osteogenicprogenitor cells, pre-osteoblasts, bone forming cells, cartilage formingcells, stem cells, and other progenitor cell types. These cells may beautogenic, allogeneic, or xenogenic. The cells may be delivered to thematrix via carriers made from gelatin, fibrin, cellulose, syntheticextracellular matrices, polymers, and other biocompatible carriers. Thecells may be injected into the hydrated matrix and then placed inculture media. These cell seeded constructs may be used for implantationinto patients for regeneration of tissue, or as 3-D cell culture modelsfor research or drug screening purposes.

The demineralized bone matrices of the present invention havesubstantial applicability and utility over prior art methods andmaterials by means of improved conformability relative to itssponge-like matrix while minimizing damage to (or removal of) nativegrowth factors during demineralization An additional embodiment is forimplantation into bone or cartilage defect sites with unique shapes, andsizes for improved bone graft success or cartilage repair success.Additionally, improved conformability of the sponge-like demineralizedbone graft matrix is easily incorporated into various cages and otherdevices for bone graft procedures.

The American Academy of Orthopedic Surgeons and the American Associationof Tissue Banks have suggested a list of attributes for an ideal bonegraft substitute (BGS), but these groups have also stated that the idealhas yet to be achieved. These cited properties include, for example andnot by limitation: (1) biocompatible; (2) bioresorbable; (3) osteogenic(i.e., capacity of the cellular elements of the transplanted graft tosurvive and directly form new bone); (4) osteoconductive; (5)osteoinductive; (6) structurally similar to bone; (7) easy to use; (8)malleable; and (9) deformable. The demineralized cancellous bone matrixof the present invention meets all of these criteria by itself, exceptfor having osteogenic properties. However, if the demineralizedcancellous bone matrix is infiltrated with bone marrow aspirate or ifcoated or infiltrated with stem cells, the demineralized cancellous bonematrices would meet all of the criteria listed for an ideal implant bythe Academy of Orthopedic Surgeons and by the American Association ofTissue Banks

The following examples will illustrate the practice of the presentinvention in further detail. It will be readily understood by thoseskilled in the art that the following methods, formulations, andcompositions of novel compounds of the present invention, as generallydescribed and illustrated in the examples herein, are to be viewed asexemplary of the principles of the present invention, and not asrestrictive to a particular structure or process for implementing thoseprinciples. Thus, Examples 1-6, are not intended to limit the scope ofthe invention, as claimed, but are merely representative of exemplaryembodiments of the invention.

EXAMPLES Example 1

A method for preparing demineralized cancellous bone pieces as describedin the present invention may include the steps of: (1) adding from 1-300grams of cancellous bone matrix to 10-4500 mL of 0.3-2.0 M hydrochloricacid (HCl) in a suitable reaction vessel; (2) stirring the vesselcontents for approximately 4-10 hours; (3) replacing “spent” acidsolution in the beaker every 1-4 hours; (4) removing each piece ofcancellous bone matrix every 5-90 minutes and performing tests todetermine whether the block is fully compressible; and (5) transferringpieces of cancellous bone matrix that are fully compressible to aneutralizing solution having a pH of >4 and returning the pieces ofcancellous bone matrix that are not fully compressible to the acidcontaining reaction vessel to continue for further demineralization andrepeated compression testing as described above.

Example 2 Use of Ozone to Improve Function of Demineralized CancellousBone Matrix

A method for improved function of demineralized cancellous bone matrixby treating said bone with ozone during the processing of the tissue mayinclude the steps of: (1) placing demineralized cancellous bone matrixin an ozone enriched solution containing microbubbles; (2) withcontinual replacement of the solution containing an ozone concentrationof 0.1 to 400 ppm; (3) with an exposure time of 0.1 to 7 hours; at atemperature range of the ozone solution of −20 to 50 C. Ozone solutiontreatment of the bone could also take place prior to demineralizationusing the same parameters discussed above.

Example 3 Clinical Applications for Demineralized Cancellous Bone Matrix

The following are examples of clinical applications and uses for thenovel demineralized cancellous bone matrix:

Use in Spinal Implants: This example demonstrates some of the biologicand mechanical properties of demineralized cancellous bone matrices anddemineralized cancellous bone matrix compounds prepared in accordancewith the present invention when used in association with a mechanicaldevice to create a fusion and facilitate healing between surfaces ofadjacent vertebral bodies.

The novel demineralized cancellous bone matrices of the presentinvention may be placed in a space or void provided by an anteriorspinal implant (e.g., spinal cage or other device comprised of metal,bone, plastic, or other composite material). The demineralized bonegraft matrix compresses allowing it to be fit into various shaped spaceswithout fracturing the demineralized cancellous bone matrix and thenexpands to fill the void within the device. As the demineralizedcancellous bone matrix is hydrated, without oozing from the device andwithout dissolving in the presence of saline, irrigant, or body fluids,the demineralized cancellous bone matrix expands to tightly abut theadjacent bone surfaces creating an osteogenic, osteoinductive, andosteoconductive bridge that may be used alone or in conjunction withother bone putties or gels, active biologic or pharmacologic coatings,blood or bone marrow aspirate.

Alternatively, a demineralized cancellous bone matrix compound,comprised of various pieces of demineralized cancellous bone matrix withother constituents (for example, with or without bone marrow aspirate orplatelet gel), can be placed in a space or void provided by an anteriorspinal implant (spinal cage or other device comprised of metal, bone,plastic, or other composite material). The demineralized cancellous bonematrix compound compresses to allow it to be fit into various shapedspaces without fracturing and then expands to fill the void within thedevice without oozing from the device, without dissolving in thepresence of saline, irrigant, or body fluids, the demineralizedcancellous bone matrix compound expands to tightly abut the adjacentbone surfaces creating an osteogenic, osteoinductive, andosteoconductive bridge that may be used alone or in conjunction withother bone putties or gels, active biologic or pharmacologic coatings,blood or bone marrow aspirate.

Use in Structural Spinal Cortical/Cancellous Allograft This exampledemonstrates that a demineralized cancellous bone matrix ordemineralized cancellous bone matrix compound prepared in accordancewith the present invention may be used in conjunction with structuralspinal cortical or cortical/cancellous allograft. A dowel or precisionmilled spinal allograft cut from the tibia, femur, humerus, fibula,tarsal or other bone provides structural support between two adjacentvertebral bodies like a spinal implant. When the dowel is hollow, thedemineralized cancellous bone matrix may be placed in the center of thedowel to create a fusion and facilitate healing between surfaces of theadjacent vertebral bodies. The demineralized cancellous bone matrix maybe cut into a ring configuration or other variable shape and design tofit around the outside of cortical allograft to create a fusion andfacilitate bone healing.

Use in Delayed Union or Non-Unions of Bone: This example demonstrates anexemplary embodiment of using the unique mechanical and biologicproperties of demineralized cancellous bone matrices prepared inaccordance with the processes, methodologies, and techniques of thepresent invention to create a healing bridge across delayed unions ofbone or non-unions of bone by placing a demineralized cancellous bonematrix across the pathologic space.

A canal may be drilled from one healthy bone end across the non-healingspace and into the second healthy bone. Using a novel device consistingof a size rasp, an inserter with a plunger, a demineralized cancellousbone matrix formed as a cylinder or dowel with or without activebiologic or pharmacologic coatings, may be placed into the canal, thusbridging one healthy bone with another. The novel characteristics of thedemineralized cancellous bone matrix allows it to be compressed into theinserter and when hydrated in the canal with saline, blood, bone marrowaspirate, or other fluid substance, the demineralized cancellous bonematrix expands to tightly fill the space. Because the demineralizedcancellous bone matrix is elastic and will deform to compressive,tensile, torsional, and bending forces, some movement at the non-unionsite will not cause the bridging graft to fatigue and fracture. Ascontemplated herein, the demineralized cancellous bone matrix of thepresent invention, because of its structural features, may be used withall manner of orthopedic fixation such as plates and screws:intramedullary fixation, pins or wires, external fixation devices, acast, splint, or brace.

Use in Distraction Osteogenesis: This example demonstrates an exemplaryembodiment of using the present invention to promote and hasten bonehealing in distraction-osteogenesis (bone lengthening or transport). Ademineralized cancellous bone matrix bridge may be placed at thecorticotomy or osteotomy site, either at the time of surgical creationof the bone defect or some time later. The demineralized cancellous bonematrix may be placed within the canal or within a distraction callouseither with or without use of the insertion device or a variant of thedevice.

A demineralized cancellous bone matrix bridge may be used indistraction-osteogenesis with all manner of orthopedic fixation such asplates and screws, intramedullary fixation, pins or wires, externalfixation devices, a cast, splint, or brace.

Use in Fracture Healing: This example demonstrates an exemplaryembodiment of using the present invention to promote fracture healing atacute fracture sites.

A canal may be drilled from one bone end across the fracture space andinto the second bone. A bone graft application kit, in accordance withthe present invention, may include a size rasp, an inserter with aplunger, a demineralized cancellous bone matrix cylinder or dowel withor without active biologic or pharmacologic coatings, which may beplaced into the canal, thus bridging one healthy bone with another. Thenovel characteristics of the demineralized cancellous bone matrix allowsit to be compressed into the inserter and when hydrated in the canalwith saline, blood, bone marrow aspirate, or other fluid substance, thedemineralized cancellous bone matrix will expand to tightly fill thespace. Because the demineralized cancellous bone matrix is elastic andwill deform to compressive, tensile, torsional, and bending forces, somemovement at the nonunion site will not cause the bridging graft tofatigue and fracture.

The demineralized cancellous bone matrix may be placed into themedullary space at the fracture site at the time of surgical repaireither with the inserter or manually. It can be placed in the form of acylinder or dowel or as fragment pieces, as desired. The demineralizedcancellous bone matrix bridge in accordance with the present inventionmay be used with all manner of orthopedic fixation such as plates andscrews, intramedullary fixation, pins or wires, external fixationdevices, a cast, splint, or brace.

Use in Arthrodesis Healing: This example demonstrates an exemplaryembodiment of using the present invention to enhance and promotesuccessful healing at an arthrodesis site where the joint between twobones is removed and an attempt is made to obtain bone fusion orarthrodesis between the remaining bones; joints typically fused orarthrodesis are the bones of the fingers, toes, wrist, foot and ankleThe ankle joint is at especially high risk for failure of fusion. Otherjoints commonly fused include the shoulder, elbow, hip, and knee joints.The demineralized cancellous bone matrix of the present invention can beused with anterior and posterior spinal segments, including facetjoints, any moveable or nonmovable joint, including sacro-iliac joints,pubis, and acromio-clavicular joint, and stemo-clavicular joints.

A canal may be drilled from one healthy bone end across the arthrodesissite and into the second healthy bone. Using a novel device consistingof a size rasp, an inserter with a plunger, a demineralized cancellousbone matrix formed as a cylinder or dowel with or without activebiologic or pharmacologic coatings, the demineralized cancellous bonematrix may be placed into the canal, thus bridging one healthy bone withanother. The novel characteristics of the demineralized cancellous bonematrix allow it to be compressed into the inserter and when hydrated inthe canal with saline, blood, bone marrow aspirate, or other fluidsubstance, the demineralized cancellous bone matrix will expand totightly fill the space. Because the demineralized cancellous bone matrixis elastic and will deform to compressive, tensile, torsional, andbending forces, some movement at the non-union site will not cause thebridging graft to fatigue and fracture. The drill used may or may not bethe same diameter as drills used with standard internal fixationdevices, and may or may not be used with cannulated drills.

Use in Improving Fixation in Arthroplasties: A novel device inaccordance with the present invention may be used to fill defects inbone and hasten and/or facilitate healing of bone. Demineralizedcancellous bone matrices prepared in accordance with the processes,methodologies, and techniques of the present invention may be placedwithin a defect in bone resulting from trauma, cyst, tumor, previoussurgery, or infection. The demineralized cancellous bone matrix may bepacked in the defect as a single block or in multiple fragments thatmight range in size from 2 mm to several centimeters. The demineralizedcancellous bone matrix and smaller fragments of bone matrix (e.g.,compound) may be used in association with joint athroplasties to improvefixation and fill defects such as those adjacent to acetabular cups inthe pelvis, around femoral stems, adjacent to knee components of thedistal femur, proximal tibia and adjacent to components reconstructingthe joints of the hand, wrist, elbow, shoulder, foot, ankle, or otherarticulating surfaces.

The unique structural and functional features of the demineralizedcancellous bone matrices of the present invention allow for compressionto facilitate placement into various shaped spaces or cavities withoutfracturing. The demineralized cancellous bone matrix expands to fill thevoid within the device as it is hydrated without oozing from the device,without dissolving in the presence of saline, irrigant, or body fluids;the demineralized cancellous bone matrix expands to tightly about theadjacent bone surfaces creating an osteogenic, osteoinductive, andosteoconductive bridge that may be used alone or in conjunction withother bone putties or gels, active biologic or pharmacologic coatings,blood or bone marrow aspirate.

Use in Cartilage Repair and Regeneration: This example demonstrates anexemplary embodiment of using the present invention for cartilage repairby placement of the matrix in a lesion in the cartilage to encouragecartilage regeneration. The present invention allows for compression tofacilitate placement into various cartilage defects or cavities withinand in association with cartilage. The hydrated demineralized cancellousbone matrix expands to fill the void within the cartilage and may absorbblood or bone marrow. The demineralized cancellous bone matrix may becoated or injected with growth factors or stem cells to further enhancerepair and regeneration of cartilage.

Use in Oral Surgery: This example demonstrates an exemplary embodimentof using the present invention for reconstructing mandible and maxillabone in reconstructive oral surgery. A demineralized cancellous bonematrix of the present invention may be placed into cavities or spaces inthe jaw and maxilla as graft to recreate lost bone. The demineralizedcancellous bone matrix may be used with or without demineralizedcortical bone powder, with or without carriers or other active biologicor pharmacologic agents. At least two presently preferred uses of thepresent invention are contemplated for use in oral surgery and arepresent in this example. A pre-selected and/or appropriate sizeddemineralized bone graft material in accordance with the presentinvention may be inserted in a tooth extraction socket. If appropriate,an osseous alveolar defect may also be repaired in the same fashionusing bone graft materials in accordance with the present invention. Amembrane of choice may be placed over the demineralized bone graftmaterial in accordance with the present invention and may be sutured atthe gingival level.

An appropriately sized and hydrated demineralized cancellous bone matrixprocessed in accordance with the processes, methodologies, andtechniques of the present invention may be inserted through the sinuswindow and may be placed into a surgically created sinus cavity. Thisexemplary embodiment of the present invention may have one or more ofthe following advantages over known prior art. First, ease ofapplication--the demineralized cancellous bone matrices or compoundscomprising same of the present invention may be more easily insertedinto the graft site relative to prior art graft materials and methods.As noted herein, the demineralized cancellous bone matrix may beformulated as a single piece of compressible material compared totraditional (i.e., prior art) grafting materials that may be particulateor putty like in consistency and thus may be more difficult to place ata graft site. Second, the demineralized cancellous bone matrix of thepresent invention may be compressed prior to placement at a desiredgraft site and may then expand after placement. In contrast, prior artbone graft materials need to be packed into a graft site. Third, thebone graft matrix or derived compounds may not migrate, eliminating theneed to use membranes for coverage. Finally, the demineralizedcancellous bone matrices of the present invention may result in fasterbone formation allowing faster placement of dental implants.

Use in Healing Infected Bone: This example demonstrates an exemplaryembodiment of using the present invention for enhancing or promotinghealing in the presence of infected or contaminated bone and softtissues when attempting to heal an infected non-union of bone; whenattempting to fuse an infected joint either primarily or after a failedtotal joint arthroplasty; when attempting to internally or externallyfix an acute or old fracture; when attempting to fuse an infected spinalsegment either primarily or after a previously failed spinal fusion;when attempting to lengthen and transport bone in a previously infectedbone segment. Demineralized bone graft materials treated with a elutivecoating designed to release antibiotic or anti-infective agents such as:silver sulfadiazine, chlorhexidine, gentamicin, tobramycin, vancomycinor others. Demineralized bone graft materials soaked in an antibiotic oranti-infective solution containing active agents such as: silversulfadiazine, chlorhexidine, gentamicin, tobramycin, vancomycin orothers. The demineralized bone graft material may be packed into theaffected area as a block, as smaller fragments or introduced as acylinder.

Veterbroplasty application: Osteoporosis thins the bones of some 10million Americans. Some 700,000 patients a year suffer spinal fracturesas a result. They're excruciating since sitting or standing compressesthe broken vertebra. About two-thirds of patients become pain-free aftera few months of bed rest, but the rest have chronic pain. And spinalfractures accumulate, stealing height and causing digestion andbreathing problems. Using a veterbroplasty approach that is currentlyavailable, the sponge-like bone material incorporated into thebiodegradable glue would be injected into the crushed vertebra, where itwill expand and provide immediate pain relief and supporting structurefor the vertebra, and agents which will stimulate bone regrowth. Currentvertebroplasty techniques use a cement (e.g., methylmethacrylate glue)to stabilize the bone and to prevent or delay further collapse. There isevidence that patients receive relief with this technique, with smallstudies suggesting anywhere from 75 to 90 percent of patients get painrelief.

A newer technique called Kyphoplasty is more complicated. First acatheter bearing a balloon may be threaded into the cracked vertebra.Inflating the balloon with a special liquid jacks up the collapsed boneso the cement can then be injected, restoring some height. The advantageof the invention is that the cement used in the currently availableprocedures does not encourage bone growth. The pain relief is usuallyonly temporary, and within a few months the patients are again havingproblems. Our use of bone compatible materials, and materials thatencourage bone growth will facilitate the potential for a more permanentrecovery of structure and function of osteoporotic bone. The expandablenature of the sponge-like bone material combined with biodegradeableglue could be exploited to provide immediate height restoration andvertebral stability for the patient.

Example 4 Delivery of Bioactives to Wound Site

A method delivery of bioactives using the demineralized cancellous bonematrix as a carrier via; (1) bioactive impregnation of the matrix byplacing the dehydrated or hydrated demineralized cancellous bone matrixin a solution containing the bioactive, whereby the matrix ‘soaks’ upthe solution, followed by air or freeze drying; (2) or by coating thedemineralized cancellous bone matrix with a hydrogel, polymer or othermaterial that contains a bioactive; (3) or by injecting a solutioncontaining a bioactive into the matrix.

These and other active proteins could be infiltrated, impregnated orinjected into the demineralized cancellous bone matrix or coated ontothe demineralized surface. The proteins could be placed adjacent to thedemineralized cancellous bone matrix by way of another carrier and thusimparted to the immediate surgical bed. The demineralized cancellousbone matrices make an ideal carrier for these proteins because of itsdescribed mechanical properties, it elasticity, its flexibility, itsosteoinductive properties, its osteoconductive properties, itsabsorbency and ability to hold onto fluids when hydrated.

The demineralized cancellous bone matrix compound prepared in accordancewith the processes, methodologies, and techniques of the presentinvention can be combined with these and other active proteins and couldbe mixed into the demineralized cancellous bone matrix compound orcoated onto the demineralized particle surface or surface of anothersubstance used with the bone compound. The proteins could be placedadjacent to the demineralized cancellous bone matrix by way of anothercarrier and thus imparted to the immediate surgical bed. Thedemineralized cancellous bone matrix makes an ideal carrier for theseproteins because of its described mechanical properties, it elasticity,its flexibility, its osteoinductive properties, its osteoconductiveproperties, its absorbency and ability to hold onto fluids whenhydrated.

Example 5 Creation of ‘Inert’ Bone Matrix

Demineralized bone matrix may be processed in such a way as topurposefully reduce the availability of growth factors within the matrixby utilizing known adverse treatments. This will provide an ‘inert’matrix, consisting of mostly extracellular components, primarilycollagen, without significant signal molecule content. Such a matrix maybe desirable in some clinical and research settings. Further processingdemineralized bone by hydrogen peroxide exposure is one method toaccomplish this goal.

Example 6 Use of Demineralized Cancellous Bone Matrix as a 3-D Scaffold

A method for the use of the demineralized cancellous bone matricesprepared in accordance with the processes, methodologies, and techniquesof the present invention as material for the three dimensional (3-D)culturing of cells, (1) the cells are delivered to the matrix viacarriers made from gelatin, fibrin, cellulose, synthetic extracellularmatrices, polymers, and other biocompatible carriers (2) or the cellsare placed in culture directly onto the matrix; (3) or the cells areinjected into the hydrated matrix and then placed in culture media; (4)complete nutritive medias is used in cultures containing thedemineralized cancellous bone matrix with cells; (5) additional mediacomponents of additives such as cell differentiation factors; (6) the3-D matrix in vitro cell culture continues until mature tissue formationoccurs, and then is implanted; (7) or conversely, may be transplantedshortly after the cells are associated with the matrix, with tissueregeneration occurring in vivo; (8) the demineralized cancellous bonematrix cell culture constructs will be used to perform drug or chemicalscreening to assess trophic or toxic agents by exposing cell seededconstructs in vitro to chemicals of interest and assessing cellviability or function; (9) kits will consist of samples of prepareddemineralized cancellous bone matrix, with and without reagents or cellsappropriate for the specific field of interest.

These cultures of cells in the demineralized cancellous bone matrix maybe used to grow bone or cartilage for transplantation to repair bone orcartilage defects or other tissue or organ defects in humans or animals.Cell seeded scaffolds may be cultured in vitro until mature tissueformation occurs, and then implanted, or conversely, may be transplantedshortly after the cells are associated with the matrix, with tissueregeneration occurring in vivo. For example, chondrocytes may be grownin vitro on the demineralized cancellous bone matrix, to form cartilagetissue that may then be implanted into an area of injured cartilage torepair and regenerate the tissue.

The demineralized cancellous bone matrix cell culture constructs mayalso be used as a research model to perform drug or chemical screeningto assess trophic growth enhancing or stem cell differentiation agentsor possible toxic agents in a 3-D culture setting. Current testing isoften performed using 2-D culturing of cells and it is known to thosefamiliar in the art that results from 2-D cultured cells are oftendifferent from those cells cultured in 3-D matrices, which is a morenatural environment to cells of all types. Kits may provide samples ofprepared demineralized cancellous bone matrix, with and without reagentsor cells appropriate for the specific field of interest.

Demineralized cancellous bone matrix readily absorbs, within thecollagen fibers, many kinds of bioactives, as well as stains and dyesand therefore extends said bone matrices uses to cellularattachment/adhesion and growth research where the bioactives, stains,and dyes elute from the matrix surface. Demineralized cancellous bonematrix can be sliced into thin sheets for improved observation ofcellular activities and remodeling of the extracellular matrix.Xenogenic materials are readily available, and hence particularlyattractive for research applications.

Cancer cells can also be grown on this matrix to assess chemotherapeuticagents. Autologous cancer cells may be used, and chemotherapeutic agentscould be screened to tailor the specific anti-cancer drug combinationmost effective for tumor suppression or elimination in a given patient.

As will be appreciated, the present invention may be embodied in otherspecific forms without departing from its spirit or essentialcharacteristics. The described embodiments are to be considered in allrespects only as illustrative, and not restrictive.

Although the present invention has been described with reference topreferred embodiments, workers skilled in the art will recognize thatchanges may be made in form and detail without departing from the spiritand scope of the invention.

1. A method for producing a demineralized cortical bone matrix, themethod comprising: placing a cortical bone body in a first processingsolution comprising an acid at a pH of greater than about pH=0 todemineralize the cortical bone body; periodically removing the corticalbone body from the first processing solution at specific time intervalsto perform a bending test on the cortical bone body, wherein the testcomprises applying a bending force in a range from about 10 g-force/cm²to about 4000 g-force/cm², wherein the bending force does not cause thecortical bone body to fracture; and after the cortical bone body bendswithout fracturing, exposing the cortical bone body to a secondprocessing solution.
 2. The method of claim 1, wherein the cortical bonebody regains its original shape, structure, and size after the bendingforce is removed.
 3. The method of claim 1, wherein the cortical bonebody has a volume greater than about 4 cubic millimeters.
 4. The methodof claim 1, wherein the cortical bone body is fragmented.
 5. The methodof claim 1, wherein the second processing solution has a pH greater thanabout
 4. 6. The method of claim 1, wherein the second processingsolution has a pH ranging from about 7 to about
 14. 7. The method ofclaim 1, wherein the second processing solution comprises a buffer. 8.The method of claim 1, wherein the second processing solution isaqueous-based.
 9. The method of claim 1, wherein the second processingsolution is organic and is capable of neutralizing the acid within andon the cortical bone body.
 10. The method of claim 1, whereindeterioration, inactivation, or elimination of an intrinsic growthfactor within the demineralized cortical bone matrix is minimized. 11.The method of claim 10, wherein the intrinsic growth factor is IGF-1.12. The method of claim 1, wherein an intrinsic growth factor within thedemineralized cortical bone matrix is maximally preserved.
 13. Themethod of claim 12, wherein the intrinsic growth factor is IGF-1. 14.The method of claim 1, wherein deterioration, inactivation, orelimination of intrinsic bone morphogenic proteins within thedemineralized cortical bone matrix is minimized.
 15. The method of claim1, wherein intrinsic bone morphogenic proteins within the demineralizedcortical bone matrix are maximally preserved.
 16. The method of claim 1,wherein the cortical bone body is selected from the group consisting ofautogenic bone, allogeneic bone, xenogenic bone, and combinationsthereof
 17. The method of claim 1, wherein the demineralized corticalbone matrix contains less than about two percent of a mineral by weight.18. The method of claim 17, wherein the mineral is selected from thegroup consisting of calcium, magnesium, and phosphate.
 19. The method ofclaim 1, wherein the cortical bone body comprises a block.
 20. Themethod of claim 1, wherein the specific time intervals range from about5 minutes to about 4 hours.
 21. The method of claim 1, wherein thespecific time intervals range from about 5 minutes to about 4 hours. 22.The method of claim 1, wherein the cortical bone body comprises a strip.23. The method of claim , wherein a length of the cortical bone bodyranges from about 5 millimeters to about 500 millimeters.
 24. The methodof claim 1, wherein the cortical bone body comprises a block.
 25. Themethod of claim 1, wherein the bending force ranges from about 10g-force/cm² to about 1000 g-force/cm².
 26. The method of claim 1,wherein the pH of the first processing solution is from about pH=0 toabout pH=0.5.
 27. The method of claim 1, wherein the pH of the firstprocessing solution is about pH=0.2.
 28. The method of claim 1, whereinafter exposing the cortical bone body to a second processing solution,the cortical bone body contains less than 2 percent residual calcium byweight.